Quick priming connectors for blood circuit

ABSTRACT

A connector system is provided for use in priming a fluid circuit. The system includes a first connector and a second connector. The first connector is configured to couple with one end of a conduit. The first connector has a gas permeable membrane, a main lumen extending from the gas permeable membrane, and a second lumen. The second lumen has a first end configured to couple with a fluid source and a second end in fluid communication with the main lumen. The second connector is configured to couple with an end of a cannula. The second connector has an end configured to be inserted through the gas permeable membrane into the first connector, whereby fluid communication can be established between the main lumen of the first connector and the cannula lumen.

RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.11/370,225, filed Mar. 6, 2006, which is pending and the entire contentof which is hereby incorporated by reference herein.

BACKGROUND

1. Field of the Invention

This application is directed to a system and method for removing anunwanted gas or fluid from a fluid circuit and more particularly isdirected to removing gas from a blood circuit.

2. Description of the Related Art

Dialysis and other medical procedures have been implemented to treatblood in patients. In dialysis, blood is removed from and then returnedto the patient after being treated. The treatment removes impuritiesfrom the blood, a function performed by the kidney in a healthy person.Typically, blood is withdrawn via a first catheter, forced through afilter, and returned to the patient via a second catheter.

Various techniques have been developed to apply these systems in amanner that prevents embolic matter, including gases, from enteringpatient's blood stream. For example, a technique can be employed wheretwo catheters are connected together. Prior to this connection, thecatheters are filled as much as possible at the ends being connected.Then the ends of the two catheters are coupled together. This techniqueis not optimal at least because it requires spillage of some of thefluid in the catheters to significantly reduce the potential forintroduction of embolic matter, e.g., gas. Additionally, this techniqueusually requires at least two people to fill the catheters and couplethem together.

SUMMARY

It would be advantageous to have devices and techniques that enablequickly priming two fluid conveying portions of a fluid circuit. Suchpriming would enable the two fluid conveying portions to be connectedtogether whereby the risk of introduction of embolic matter or material,e.g., gas, is reduced or eliminated. Preferably such system will be easyto use and will result in minimum spillage of fluids.

In one embodiment, a system for priming a liquid circuit is provided.The system includes a tube assembly and a cannula assembly. The tubeassembly includes a tube and a tube connector. The tube connector has ahousing with a lumen therethrough having a housing cross-sectional area.The housing also comprising a first port, a membrane extending acrossthe first port, a second port configured to couple with the tube, and athird port configured to couple with a source of liquid. The cannulaassembly comprises a cannula and a cannula connector. The cannulaincludes a first end and a second end configured to couple with a sourceof liquid to be conveyed in the circuit. The cannula defines a portionof a cannula lumen having a first cross-sectional area. The cannulaconnector includes a piercing member that defines a portion of thecannula lumen having a second cross-sectional area. The secondcross-sectional area is substantially the same as the firstcross-sectional area. The piercing member is configured to pierce themembrane upon joining the cannula connector to the tube connector.

In one variation of the system described in the preceding paragraph, thesystem is for priming a blood-flow circuit coupled with a pump. Thesystem includes a pump tube assembly and a cannula assembly. The pumptube assembly includes a pump tube and a pump tube connector. The pumptube connector has a housing with a lumen therethrough having a housingcross-sectional area. The pump tube connector has a first port, amembrane extending across the first port, a second port configured tocouple with the pump tube, and a third port configured to couple with asource of biocompatible liquid. The cannula assembly includes a cannulahaving a second end configured to couple with a blood vessel.

In another implementation, a method of priming a blood circuit isprovided. The blood circuit comprises a pump, a pump tube having a pumptube lumen fluidly coupled with the pump, a gas permeable membraneextending across the pump tube lumen, a cannula having a cannula lumenthat extends between a first end and a second end and a piercingstructure adjacent to the first end. The method comprises: forcing abiocompatible liquid into the pump tube lumen at a location between thegas permeable membrane and the pump to pressurize the pump tube lumenand to force gas in the pump tube lumen through the membrane; andpiercing the membrane with the piercing structure such that the cannulalumen and the pump tube lumen are in fluid communication.

In another embodiment, a connector system for use in priming a fluidcircuit is provided. The fluid circuit has a pump, a conduit having afirst end coupled with the pump and a second end, a cannula having afirst end and a second end configured to fluidly couple with a firstfluid source, and a cannula lumen extending between the first and secondends. The system includes a first connector and a second connector. Thefirst connector is configured to couple with the second end of theconduit. The first connector has a gas permeable membrane, a main lumenextending from the gas permeable membrane, and a secondary lumen. Thesecond lumen has a first end configured to couple with a second fluidsource and a second end in fluid communication with the main lumen. Thesecond connector is configured to couple with the first end of thecannula. The second connector has an end configured to be insertedthrough the gas permeable membrane into the first connector, wherebyfluid communication can be established between the main lumen of thefirst connector and the cannula lumen.

One variation of the embodiment set forth in the preceding paragraphinvolves a connector system for use in priming a blood circuit. In thisvariation, the cannula has a first end configured to fluidly couple witha blood vessel. The system comprises a first connector and a secondconnector. The first connector has a lumen that has a first endconfigured to couple with a source of bio-compatible liquid.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other features and advantages of the invention will now bedescribed with reference to the drawings, which are intended toillustrate and not to limit the invention.

FIG. 1 is a schematic view of one embodiment of a heart assist systemhaving multiple conduits for multi-site application, shown applied to apatient's vascular system;

FIG. 2 is a schematic view of another application of the embodiment ofFIG. 1;

FIG. 3 is a schematic view of another embodiment of a heart assistsystem having multiple conduits for multi-site application wherein eachof the conduits is applied to more than one vessel, shown applied to apatient's vascular system;

FIG. 4 is a schematic view of another embodiment of a heart assistsystem having multiple conduits for multi-site application and employinga connector with a T-shaped fitting, shown applied to a patient'svascular system;

FIG. 5 is a schematic view of an L-shaped connector coupled with aninflow conduit, shown inserted within a blood vessel;

FIG. 6 is a schematic view of another embodiment of a heart assistsystem having multiple conduits for multi-site application, shownapplied to a patient's vascular system;

FIG. 7 is a schematic view of another application of the embodiment ofFIG. 6, shown applied to a patient's vascular system;

FIG. 8 is a schematic view of another application of the embodiment ofFIG. 6, shown applied to a patient's vascular system;

FIG. 9 is a schematic view of another embodiment of a heart assistsystem having multiple conduits for multi-site application, a reservoir,and a portable housing for carrying a portion of the system directly onthe patient;

FIG. 10 is a schematic view of another embodiment of a heart assistsystem having a multilumen cannula for single-site application, shownapplied to a patient's vascular system;

FIG. 11 is a schematic view of a modified embodiment of the heart assistsystem of FIG. 10, shown applied to a patient's vascular system;

FIG. 12 is a schematic view of another embodiment of a heart assistsystem having multiple conduits for single-site application, shownapplied to a patient's circulatory system;

FIG. 13 is a schematic view of another application of the embodiment ofFIG. 12, shown applied to a patient's vascular system;

FIG. 14 is a schematic view of one application of an embodiment of aheart assist system having an intravascular pump enclosed in aprotective housing, wherein the intravascular pump is inserted into thepatient's vasculature through a non-primary vessel;

FIG. 15 is a schematic view of another embodiment of a heart assistsystem having an intravascular pump housed within a conduit having aninlet and an outlet, wherein the intravascular pump is inserted into thepatient's vasculature through a non-primary vessel;

FIG. 16 is a schematic view of a modified embodiment of the heart assistsystem of FIG. 15 in which an additional conduit is shown adjacent theconduit housing the pump, and in which the pump comprises ashaft-mounted helical thread;

FIG. 17 is a cross-sectional view of one embodiment of a system forpriming a liquid circuit;

FIG. 18 is a perspective view of a connector system for use in primary aliquid circuit, such as that of FIG. 17;

FIG. 19 is an exploded perspective view of the connector system of FIG.18;

FIG. 20 is a perspective view of a housing for a pump tube connector,which can form a part of the connector system of FIG. 18;

FIG. 21 is a perspective view of a removable cap configured to bemounted to the housing of FIG. 20;

FIG. 22 is a perspective view of a membrane assembly including amembrane configured to be positioned between the cap of FIG. 21 and thehousing of FIG. 20; and

FIG. 23 is a perspective view of a cannula connector that is configuredto pierce the membrane of the membrane assembly of FIG. 22.

DETAILED DESCRIPTION

Turning now to the drawings provided herein, more detailed descriptionsof various embodiments of heart assist systems and cannulae and cannulaeconnector systems for use therewith are provided below. The connectorsystems can be used to couple two conduits of a fluid circuit, such as aconduit that can be connected to a pump and a cannula connectable orinsertable into a blood vessel. As discussed below in connection withFIGS. 17-23, the liquid circuit primary systems, connector systems, andtechniques described below can be applied outside the context ofvascular access and medical treatment, for example, these systems andtechniques are applicable whenever it is desirable to prime a fluidcircuit such that foreign matter, particularly gas, is excluded.

FIGS. 1-16 illustrate some blood supplementation systems with which thepriming systems, connectors systems, and priming techniques can be used.Other environments in which the connector system can be deployed includecircuits for circulating or conveying biological fluids, such as wholeblood, plasma, or other subsets of whole blood, in connection with othertreatment techniques.

I. Extracardiac Heart Assist Systems and Methods

A variety of cannulae and cannula assemblies are described herein thatcan be used in connection with a variety of heart assist systems thatsupplement perfusion. Such systems preferably are extracardiac innature. In other words, the systems supplement blood perfusion, withoutthe need to interface directly with the heart and aorta. Thus, thesystems can be applied without major invasive surgery. The systems alsolessen the hemodynamic burden or workload on the heart by reducingafterload, impedance, and/or left ventricular end diastolic pressure andvolume (preload). The systems also advantageously increase peripheralorgan perfusion and provide improvement in neurohormonal status. Asdiscussed more fully below, the systems can be applied using one or morecannulae, one or more vascular grafts, and a combination of one or morecannulae and one or more vascular grafts. For systems employingcannula(e), the cannula(e) can be applied through multiple percutaneousinsertion sites (sometimes referred to herein as a multi-siteapplication) or through a single percutaneous insertion site (sometimesreferred to herein as a single-site application).

A. Heart Assist Systems and Methods Employing Multi-Site Application

With reference to FIG. 1, a first embodiment of a heart assist system 10is shown applied to a patient 12 having an ailing heart 14 and an aorta16, from which peripheral brachiocephalic blood vessels extend,including the right subclavian artery 18, the right carotid artery 20,the left carotid artery 22, and the left subclavian artery 24. Extendingfrom the descending aorta is another set of peripheral blood vessels,the left and right iliac arteries which transition into the left andright femoral arteries 26, 28, respectively. As is known, each of thearteries 16, 18, 20, 22, 24, 26, and 28 generally conveys blood awayfrom the heart. The vasculature includes a venous system that generallyconveys blood to the heart. As will be discussed in more detail below,the heart assist systems described herein can also be applied tonon-primary veins, including the left femoral vein 30.

The heart assist system 10 comprises a pump 32, having an inlet 34 andan outlet 36 for connection of conduits thereto. The pump 32 preferablyis a rotary pump, either an axial type or a centrifugal type, althoughother types of pumps may be used, whether commercially-available orcustomized. The pump 32 preferably is sufficiently small to be implantedsubcutaneously and preferably extrathoracically, for example in thegroin area of the patient 12, without the need for major invasivesurgery. Because the heart assist system 10 is an extracardiac system,no valves are necessary. Any inadvertent backflow through the pump 32and/or through the inflow conduit would not harm the patient 12.

Regardless of the style or nature chosen, the pump 32 is sized togenerate blood flow at subcardiac volumetric rates, less than about 50%of the flow rate of an average healthy heart, although flow rates abovethat may be effective. Thus, the pump 32 is sized and configured todischarge blood at volumetric flow rates anywhere in the range of 0.1 to3 liters per minute, depending upon the application desired and/or thedegree of need for heart assist. For example, for a patient experiencingadvanced congestive heart failure, it may be preferable to employ a pumpthat has an average subcardiac rate of 2.5 to 3 liters per minute. Inother patients, particularly those with minimal levels of heart failure,it may be preferable to employ a pump that has an average subcardiacrate of 0.5 liters per minute or less. In yet other patients it may bepreferable to employ a pump that is a pressure wave generator that usespressure to augment the flow of blood generated by the heart.

In one embodiment, the pump 32 is a continuous flow pump whichsuperimposes continuous blood-flow on the pulsatile aortic blood-flow.In another embodiment, the pump 32 has the capability of synchronousactuation; i.e., it may be actuated in a pulsatile mode, either incopulsating or counterpulsating fashion.

For copulsating action, it is contemplated that the pump 32 would beactuated to discharge blood generally during systole, beginningactuation, for example, during isovolumic contraction before the aorticvalve opens or as the aortic valve opens. The pump 32 would be staticwhile the aortic valve is closed following systole, ceasing actuation,for example, when the aortic valve closes.

For counterpulsating actuation, it is contemplated that the pump 32would be actuated generally during diastole, ceasing actuation, forexample, before or during isovolumic contraction. Such an applicationwould permit and/or enhance coronary blood perfusion. In thisapplication, it is contemplated that the pump 32 would be static duringthe balance of systole after the aortic valve is opened, to lessen theburden against which the heart must pump. The aortic valve being openencompasses the periods of opening and closing, wherein blood is flowingtherethrough.

It should be recognized that the designations copulsating andcounterpulsating are general identifiers and are not limited to specificpoints in the patient's heart cycle when the pump 32 begins anddiscontinues actuation. Rather, they are intended to generally refer topump actuation in which the pump 32 is actuating, at least in part,during systole and diastole, respectively. For example, it iscontemplated that the pump 32 might be activated to be out of phase fromtrue copulsating or counterpulsating actuation described herein, andstill be synchronous, depending upon the specific needs of the patientor the desired outcome. One might shift actuation of the pump 32 tobegin prior to or after isovolumic contraction or to begin before orafter isovolumic relaxation.

Furthermore, the pulsatile pump may be actuated to pulsateasynchronously with the patient's heart. Typically, where the patient'sheart is beating irregularly, there may be a desire to pulsate the pump32 asynchronously so that the perfusion of blood by the heart assistsystem 10 is more regular and, thus, more effective at oxygenating theorgans. Where the patient's heart beats regularly, but weakly,synchronous pulsation of the pump 32 may be preferred.

The pump 32 is driven by a motor 40 and/or other type of drive means andis controlled preferably by a programmable controller 42 that is capableof actuating the pump 32 in pulsatile fashion, where desired, and alsoof controlling the speed or output of the pump 32. For synchronouscontrol, the patient's heart would preferably be monitored with an EKGin which feedback would be provided the controller 42. The controller 42is preferably programmed by the use of external means. This may beaccomplished, for example, using RF telemetry circuits of the typecommonly used within implantable pacemakers and defibrillators. Thecontroller may also be autoregulating to permit automatic regulation ofthe speed, and/or regulation of the synchronous or asynchronouspulsation of the pump 32, based upon feedback from ambient sensorsmonitoring parameters, such as pressure or the patient's EKG. It is alsocontemplated that a reverse-direction pump be utilized, if desired, inwhich the controller is capable of reversing the direction of either thedrive means or the impellers of the pump. Such a pump might be usedwhere it is desirable to have the option of reversing the direction ofcirculation between two blood vessels.

Power to the motor 40 and the controller 42 may be provided by a powersource 44, such as a battery, that is preferably rechargeable by anexternal induction source (not shown), such as an RF induction coil thatmay be electromagnetically coupled to the battery to induce a chargetherein. Alternative power sources are also possible, including a devicethat draws energy directly from the patient's body; e.g., the patient'smuscles, chemicals or heat. The pump can be temporarily stopped duringrecharging with no appreciable life threatening effect, because thesystem only supplements the heart, rather than substituting for theheart.

While the controller 42 and power source 44 are preferably pre-assembledto the pump 32 and implanted therewith, it is also contemplated that thepump 32 and motor 40 be implanted at one location and the controller 42and the power source 44 be implanted in a separate location. In onealternative arrangement, the pump 32 may be driven externally through apercutaneous drive line or cable, as shown in FIG. 16. In anothervariation, the pump, motor and controller may be implanted and poweredby an extracorporeal power source. In the latter case, the power sourcecould be attached to the side of the patient to permit fully ambulatorymovement.

The inlet 34 of the pump 32 is preferably connected to an inflow conduit50 and an outflow conduit 52 to direct blood flow from one peripheralblood vessel to another. Although described as “inflow” and “outflow”conduits, these conduits can convey the blood to the pump 32 as well asaway from the pump. The conduits 50, 52 preferably are flexibleconduits, as discussed more fully below. The conduits 50, 52 are coupledwith the peripheral vessels in different ways in various embodiments ofthe heart assist system 10. As discussed more fully below, at least oneof the conduits 50, 52 can be connected to a peripheral vessel, e.g., asa graft, using an anastomosis connection, and at least one of theconduits 50, 52 can be coupled with the same or another vessel viainsertion of a cannula into the vasculature. Also, more than twoconduits are used in some embodiments, as discussed below.

The inflow and outflow conduits 50, 52 may be formed from Dacron,Hemashield, Gortex, PVC, polyurethane, PTFE, ePTFE, nylon, or PEBAXmaterials, although other synthetic materials may be suitable. Theinflow and outflow conduits 50, 52 may also comprise biologic materialsor pseudobiological (hybrid) materials (e.g., biologic tissue supportedon a synthetic scaffold). The inflow and outflow conduits 50, 52 arepreferably configured to minimize kinks so blood flow is notmeaningfully interrupted by normal movements of the patient orcompressed easily from external forces. In some cases, the inflow and/oroutflow conduits 50, 52 may come commercially already attached to thepump 32. Where it is desired to implant the pump 32 and the conduits 50,52, it is preferable that the inner diameter of the conduits 50, 52 beless than 25 mm, although diameters slightly larger may be effective.

In one preferred application, the heart assist system 10 is applied inan arterial-arterial fashion; for example, as a femoral-axillaryconnection, as is shown in FIG. 1. It should be appreciated by one ofordinary skill in the art that an axillary-femoral connection would alsobe effective using the embodiments described herein. Indeed, it shouldbe recognized by one of ordinary skill in the art that the presentinvention might be applied to any of the peripheral blood vessels in thepatient. Another application of the heart assist system 10 couples theconduits 50, 52 with the same non-primary vessel in a manner similar tothe application shown in FIG. 8 and discussed below.

FIG. 1 shows that the inflow conduit 50 has a first end 56 that connectswith the inlet 34 of the pump 32 and a second end 58 that is coupledwith a first non-primary blood vessel (e.g., the left femoral artery 26)by way of an inflow cannula 60. The inflow cannula 60 has a first end 62and a second end 64. The first end 62 is sealably connected to thesecond end 58 of the inflow conduit 50. The second end 64 is insertedinto the blood vessel (e.g., the left femoral artery 26). Although shownas discrete structures in FIG. 1, one skilled in the art would recognizethat the inflow conduit 50 and the cannula 60 may be unitary inconstruction. Any suitable technique or structure can be used to couplethe inflow conduit 50 and the cannula 60 together. Various embodimentsof suitable structures and techniques for connecting the second end 58of the inflow conduit 50 to the cannula 60 where these components areseparable are discussed in detail below in connection with FIGS. 17-23.

Where the conduit 50 is at least partially extracorporeal, the inflowcannula 60 also may be inserted through a surgical opening (e.g., asshown in FIG. 6 and described in connection therewith) orpercutaneously, with or without an introducer sheath (not shown). Inother applications, the inflow cannula 60 could be inserted into theright femoral artery or any other peripheral artery.

FIG. 1 shows that the outflow conduit 52 has a first end 66 thatconnects to the outlet 36 of the pump 32 and a second end 68 thatconnects with a second peripheral blood vessel, preferably the leftsubclavian artery 24 of the patient 12, although the right axillaryartery, or any other peripheral artery, would be acceptable. In oneapplication, the connection between the outflow conduit 52 and thesecond blood vessel is via an end-to-side anastomosis, although aside-to-side anastomosis connection might be used mid-stream of theconduit where the outflow conduit were connected at its second end toyet another blood vessel or at another location on the same blood vessel(neither shown). Preferably, the outflow conduit 52 is attached to thesecond blood vessel at an angle that results in the predominant flow ofblood out of the pump 32 proximally toward the aorta 16 and the heart14, such as is shown in FIG. 1, while still maintaining sufficient flowdistally toward the hand to prevent limb ischemia.

In another embodiment, the inflow conduit 50 is connected to the firstblood vessel via an end-to-side anastomosis, rather than via the inflowcannula 60. The inflow conduit 50 could also be coupled with the firstblood vessel via a side-to-side anastomosis connection mid-stream of theconduit where the inflow conduit were connected at its second end to anadditional blood vessel or at another location on the same blood vessel(neither shown). Further details of these arrangements and other relatedapplications are described in U.S. Pat. No. 6,889,082, issued May 3,2005, the entire contents of which is hereby incorporated by referencein its entirety and made a part of this specification.

In another embodiment, the outflow conduit 52 also is coupled with thesecond blood vessel via a cannula, as shown in FIG. 6. This connectionmay be achieved in a manner similar to that shown in FIG. 1 inconnection with the first blood vessel.

It is preferred that application of the heart assist system 10 to theperipheral or non-primary blood vessels be accomplished subcutaneously;e.g., at a shallow depth just below the skin or first muscle layer so asto avoid major invasive surgery. It is also preferred that the heartassist system 10 be applied extrathoracically to avoid the need toinvade the patient's chest cavity. Where desired, the entire heartassist system 10 may be implanted within the patient 12, eitherextravascularly, e.g., as in FIG. 1, or at least partiallyintravascularly, e.g., as in FIGS. 14-16.

In the case of an extravascular application, the pump 32 may beimplanted, for example, into the groin area, with the inflow conduit 50fluidly connected subcutaneously to, for example, the femoral artery 26proximate the pump 32. The outflow conduit would be tunneledsubcutaneously through to, for example, the left subclavian artery 24.In an alternative arrangement, the pump 32 and associated drive andcontroller could be temporarily fastened to the exterior skin of thepatient, with the inflow and outflow conduits 50, 52 connectedpercutaneously. In either case, the patient may be ambulatory withoutrestriction of tethered lines.

While the heart assist system 10 and other heart assist systemsdescribed herein may be applied to create an arterial-arterial flowpath, given the nature of the heart assist systems, i.e.,supplementation of circulation to meet organ demand, a venous-arterialflow path may also be used. For example, with reference to FIG. 2, oneapplication of the heart assist system 10 couples the inflow conduit 50with a non-primary vein of the patient 12, such as the left femoral vein30. In this arrangement, the outflow conduit 50 may be fluidly coupledwith one of the peripheral arteries, such as the left subclavian artery24. Arterial-venous arrangements are contemplated as well. In thosevenous-arterial cases where the inflow is connected to a vein and theoutflow is connected to an artery, the pump 32 should be sized to permitflow sufficiently small so that oxygen-deficient blood does not rise tounacceptable levels in the arteries. It should be appreciated that theconnections to the non-primary veins could be by one or more approachdescribed above for connecting to a non-primary artery. It should alsobe appreciated that the present invention could be applied as avenous-venous flow path, wherein the inflow and outflow are connected toseparate peripheral veins. In addition, an alternative embodimentcomprises two discrete pumps and conduit arrangements, one being appliedas a venous-venous flow path, and the other as an arterial-arterial flowpath.

When venous blood is mixed with arterial blood either at the inlet ofthe pump or the outlet of the pump the ratio of venous blood to arterialblood should be controlled to maintain an arterial saturation of aminimum of 80% at the pump inlet or outlet. Arterial saturation can bemeasured and/or monitored by pulse oximetry, laser doppler, colorimetryor other methods used to monitor blood oxygen saturation. The venousblood flow into the system can then be controlled by regulating theamount of blood allowed to pass through the conduit from the venous-sideconnection.

FIG. 3 shows another embodiment of a heart assist system 110 applied tothe patient 12. For example, the heart assist system 110 includes a pump132 in fluid communication with a plurality of inflow conduits 150A,150B and a plurality of outflow conduits 152A, 152B. Each pair ofconduits converges at a generally Y-shaped convergence 196 thatconverges the flow at the inflow end and diverges the flow at theoutflow end. Each conduit may be connected to a separate peripheralblood vessel, although it is possible to have two connections to thesame blood vessel at remote locations. In one arrangement, all fourconduits are connected to peripheral arteries. In another arrangement,one or more of the conduits could be connected to veins. In thearrangement of FIG. 3, the inflow conduit 150A is connected to the leftfemoral artery 26 while the inflow conduit 150B is connected to the leftfemoral vein 30. The outflow conduit 152A is connected to the leftsubclavian artery 24 while the outflow conduit 152B is connected to theleft carotid artery 22. Preferably at least one of the conduits 150A,150B, 152A, and 152B is coupled with a corresponding vessel via acannula. In the illustrated embodiment, the inflow conduit 150B iscoupled with the left femoral vein 30 via a cannula 160. The cannula 160is coupled to the vessel in a manner similar to that shown in FIG. 2 anddescribed in connection with the cannula 60. The cannula 160 can becoupled with one or more of the conduits 150A, 150B, 152A, 152B usingany suitable technique or structure such as any of those discussed belowin connection with FIGS. 17-23.

The connections of any or all of the conduits of the system 110 to theblood vessels may be via an anastomosis connection or via a connector,as described below in connection with FIG. 4. In addition, theembodiment of FIG. 3 may be applied to any combination of peripheralblood vessels that would best suit the patient's condition. For example,it may be desired to have one inflow conduit and two outflow conduits orvice versa. It should be noted that more than two conduits may be usedon the inflow or outflow side, where the number of inflow conduits isnot necessarily equal to the number of outflow conduits.

It is contemplated that, where an anastomosis connection is not desired,a connector may be used to connect at least one of the inflow conduitand the outflow conduit to a peripheral blood vessel. With reference toFIG. 4, an embodiment of a heart assist system 210 is shown, wherein anoutflow conduit 252 is connected to a non-primary blood vessel, e.g.,the left subclavian artery 24, via a connector 268 that comprises athree-opening fitting. In one embodiment, the connector 268 comprises anintra-vascular, generally T-shaped fitting 270 having a proximal end 272(relative to the flow of blood in the left axillary artery andtherethrough), a distal end 274, and an angled divergence 276 permittingconnection to the outflow conduit 252 and the left subclavian artery 24.The proximal and distal ends 274, 276 of the fittings 272 permitconnection to the blood vessel into which the fitting is positioned,e.g., the left subclavian artery 24. The angle of divergence 276 of thefittings 272 may be 90 degrees or less in either direction from the axisof flow through the blood vessel, as optimally selected to generate theneeded flow distally toward the hand to prevent limb ischemia, and toinsure sufficient flow and pressure toward the aorta to provide thecirculatory assistance and workload reduction needed while minimizing oravoiding endothelial damage to the blood vessel. In another embodiment,the connector 268 is a sleeve (not shown) that surrounds and attaches tothe outside of the non-primary blood vessel where, within the interiorof the sleeve, a port to the blood vessel is provided to permit bloodflow from the outflow conduit 252 when the conduit 252 is connected tothe connector 268.

Other types of connectors having other configurations are contemplatedthat may avoid the need for an anastomosis connection or that permitconnection of the conduit(s) to the blood vessel(s). For example, it iscontemplated that an L-shaped connector be used if it is desired towithdraw blood more predominantly from one direction of a peripheralvessel or to direct blood more predominantly into a peripheral vessel.Referring to FIG. 5, the inflow conduit 250 is fluidly connected to aperipheral vessel, for example, the left femoral artery 26, using anL-shaped connector 278. Of course the system 210 could be configured sothat the outflow conduit 252 is coupled to a non-primary vessel via theL-shaped connector 278 and the inflow conduit 250 is coupled via acannula, as shown in FIG. 3. The L-shaped connector 278 has an inletport 280 at a proximal end and an outlet port 282 through which bloodflows into the inflow conduit 250. The L-shaped connector 278 also hasan arrangement of holes 284 within a wall positioned at a distal endopposite the inlet port 280 so that some of the flow drawn into theL-shaped connector 278 is diverted through the holes 284, particularlydownstream of the L-shaped connector 278, as in this application. Asingle hole 284 in the wall could also be effective, depending upon sizeand placement. The L-shaped connector 278 may be a deformable L-shapedcatheter percutaneously applied to the blood vessel or, in analternative embodiment, be connected directly to the walls of the bloodvessel for more long term application. By directing some blood flowdownstream of the L-shaped connector 278 during withdrawal of blood fromthe vessel, ischemic damage downstream from the connector may beavoided. Such ischemic damage might otherwise occur if the majority ofthe blood flowing into the L-shaped connector 278 were diverted from theblood vessel into the inflow conduit 252. It is also contemplated that aconnection to the blood vessels might be made via a cannula, wherein thecannula is implanted, along with the inflow and outflow conduits.

One advantage of discrete connectors manifests in their application topatients with chronic CHF. A connector eliminates a need for ananastomosis connection between the conduits 250, 252 and the peripheralblood vessels where it is desired to remove and/or replace the systemmore than one time. The connectors could be applied to the first andsecond blood vessels semi-permanently, with an end cap applied to thedivergence for later quick-connection of the present invention system tothe patient. In this regard, a patient might experience the benefit ofthe heart assist systems described herein periodically, without havingto reconnect and redisconnect the conduits 250, 252 from the bloodvessels via an anastomosis procedure each time. Each time it is desiredto implement any of the embodiments of the heart assist system, the endcaps would be removed and a conduit attached to the connector(s)quickly.

In the preferred embodiment of the connector 268, the divergence 276 isoriented at an acute angle significantly less than 90 degrees from theaxis of the T-shaped fitting 270, as shown in FIG. 4, so that a majorityof the blood flowing through the outflow conduit 252 into the bloodvessel (e.g., left subclavian artery 24) flows in a direction proximallytoward the heart 14, rather than in the distal direction. In analternative embodiment, the proximal end 272 of the T-shaped fitting 270may have a diameter larger than the diameter of the distal end 274,without need of having an angled divergence, to achieve the same result.

With or without a connector, with blood flow directed proximally towardthe aorta 16, the result may be concurrent flow down the descendingaorta, which will result in the reduction of afterload, impedance,and/or reducing left ventricular end diastolic pressure and volume(preload). Thus, the heart assist systems described herein may beapplied so to reduce the afterload on the patient's heart, permitting atleast partial if not complete CHF recovery, while supplementing bloodcirculation. Concurrent flow depends upon the phase of operation of thepulsatile pump and the choice of second blood vessel to which theoutflow conduit is connected.

A partial external application of the heart assist systems iscontemplated where a patient with heart failure is suffering an acutedecompensation episode; i.e., is not expected to last long, or in theearlier stages of heart failure (where the patient is in New York HeartAssociation Classification (NYHAC) functional classes II or III). Withreference to FIGS. 6 and 7, another embodiment of a heart assist system310 is applied percutaneously to a patient 312 to connect twonon-primary blood vessels wherein a pump 332 and its associated drivingmeans and controls are employed extracorporeally. The pump 332 has aninflow conduit 350 and an outflow conduit 352 associated therewith forconnection to two non-primary blood vessels. The inflow conduit 350 hasa first end 356 and a second end 358 wherein the second end 358 isconnected to a first non-primary blood vessel (e.g., femoral artery 26)by way of an inflow cannula 380. The inflow cannula 380 has a first end382 sealably connected to the second end 358 of the inflow conduit 350.The inflow cannula 380 also has a second end 384 that is insertedthrough a surgical opening 386 or an introducer sheath (not shown) andinto the blood vessel (e.g., the left femoral artery 26).

Similarly, the outflow conduit 352 has a first end 362 and a second end364 wherein the second end 364 is connected to a second non-primaryblood vessel (e.g., the left subclavian artery 24, as shown in FIG. 6,or the right femoral artery 28, as shown in FIG. 7) by way of an outflowcannula 388. Like the inflow cannula 380, the outflow cannula 388 has afirst end 390 sealably connected to the second end 364 of the outflowconduit 352. The outflow cannula 388 also has a second end 392 that isinserted through surgical opening 394 or an introducer sheath (notshown) and into the second blood vessel (e.g., the left subclavianartery 24 or the right femoral artery 28). The cannulae 380 and 388 cantake any suitable form and can be coupled with the conduits 350, 352 inany suitable manner, such as by using any of the structures ortechniques discussed below in connection with FIGS. 17-23.

As shown in FIG. 7, the second end 392 of the outflow cannula 388 mayextend well into the aorta 16 of the patient 12, for example, proximalto the left subclavian artery. If desired, it may also terminate withinthe left subclavian artery or the left axillary artery, or in otherblood vessels, such as the mesenteric or renal arteries (not shown),where in either case, the outflow cannula 388 has passed through atleast a portion of a primary artery (in this case, the aorta 16). Also,if desired, blood drawn into the extracardiac system 310 describedherein may originate from the descending aorta (or an artery branchingtherefrom) and be directed into a blood vessel that is neither the aortanor pulmonary artery. By use of a percutaneous application, the heartassist system 310 may be applied temporarily without the need to implantany aspect thereof or to make anastomosis connections to the bloodvessels.

An alternative variation of the embodiment of FIG. 6 may be used whereit is desired to treat a patient periodically, but for short periods oftime each occasion and without the use of special connectors. With thisvariation, it is contemplated that the second ends of the inflow andoutflow conduits 350, 352 be more permanently connected to theassociated blood vessels via, for example, an anastomosis connection,wherein a portion of each conduit proximate to the blood vesselconnection is implanted percutaneously with a removable cap enclosingthe externally-exposed first end (or an intervening end thereof) of theconduit external to the patient. When it is desired to provide acirculatory flow path to supplement blood flow, the removable cap oneach exposed percutaneously-positioned conduit could be removed and thepump (or the pump with a length of inflow and/or outflow conduitattached thereto) inserted between the exposed percutaneous conduits. Inthis regard, a patient may experience the benefit of the presentinvention periodically, without having to reconnect and redisconnect theconduits from the blood vessels each time.

Specific methods of applying this alternative embodiment may furthercomprise coupling the inflow conduit 352 upstream of the outflow conduit350 (as shown in FIG. 8), although the reverse arrangement is alsocontemplated. It is also contemplated that either the cannula 380coupled with the inflow conduit 350 or the cannula 388 coupled with theoutflow conduit 352 may extend through the non-primary blood vessel to asecond blood vessel (e.g., through the left femoral artery 26 to theaorta 16 proximate the renal branch) so that blood may be directed fromthe non-primary blood vessel to the second blood or vice versa.

It is contemplated that a means for minimizing the loss of thermalenergy in the patient's blood be provided where any of the heart assistsystems described herein are applied extracorporeally. Such means forminimizing the loss of thermal energy may comprise, for example, aheated bath through which the inflow and outflow conduits pass or,alternatively, thermal elements secured to the exterior of the inflowand outflow conduits. Referring to FIG. 9, one embodiment comprises aninsulating wrap 396 surrounding the outflow conduit 352 having one ormore thermal elements passing therethrough. The elements may be powered,for example, by a battery (not shown). One advantage of thermal elementsis that the patient may be ambulatory, if desired. Other means that areknown by persons of ordinary skill in the art for ensuring that thetemperature of the patient's blood remains at acceptable levels whiletraveling extracorporeally are also contemplated.

If desired, the present inventive system may further comprise areservoir that is either contained within or in fluid communication withthe inflow conduit. This reservoir is preferably made of materials thatare nonthrombogenic. Referring to FIG. 9, a reservoir 398 is positionedfluidly in line with the inflow conduit 350. The reservoir 398 serves tosustain adequate blood in the system when the pump demand exceedsmomentarily the volume of blood available in the peripheral blood vesselin which the inflow conduit resides until the pump output can beadjusted. The reservoir 398 reduces the risk of excessive drainage ofblood from the peripheral blood vessel, which may occur when cardiacoutput falls farther than the already diminished baseline level ofcardiac output, or when there is systemic vasodilation, as can occur,for example, with septic shock. It is contemplated that the reservoir398 would be primed with an acceptable solution, such as saline, whenthe present system is first applied to the patient.

As explained above, one of the advantages of several embodiments of theheart assist system is that such systems permit the patient to beambulatory. If desired, the systems may be designed portably so that itmay be carried directly on the patient. Referring to FIG. 9, this may beaccomplished through the use of a portable case 400 with a belt strap402 to house the pump, power supply and/or the controller, along withcertain portions of the inflow and/or outflow conduits, if necessary. Itmay also be accomplished with a shoulder strap or other techniques, suchas a backpack or a fanny pack, that permit effective portability. Asshown in FIG. 9, blood is drawn through the inflow conduit 350 into apump contained within the portable case 400, where it is discharged intothe outflow conduit 352 back into the patient.

B. Heart Assist Systems and Methods Employing Single-Site Application

As discussed above, heart assist systems can be applied to a patientthrough a single cannulation site. Such single-site systems can beconfigured with a pump located outside the vasculature of a patient,e.g., as extravascular pumping systems, inside the vasculature of thepatient, e.g., as intravascular systems, or a hybrid thereof, e.g.,partially inside and partially outside the vasculature of the patient.

1. Single-Site Application of Extravascular Pumping Systems

FIGS. 10 and 11 illustrate extracardiac heart assist systems that employan extravascular pump and that can be applied through as a single-sitesystem. FIG. 10 shows a system 410 that is applied to a patient 12through a single cannulation site 414 while inflow and outflow conduitsfluidly communicate with non-primary vessels. The heart assist system410 is applied to the patient 12 percutaneously through a single-site tocouple two blood vessels with a pump 432. The pump 432 can have any ofthe features described in connection the pump 32. The pump 432 has aninflow conduit 450 and an outflow conduit 452 associated therewith. Theinflow conduit 450 has a first end 456 and a second end 458. The firstend 456 of the inflow conduit 450 is connected to the inlet of the pump432 and the second end 458 of the inflow conduit 450 is fluidly coupledwith a first non-primary blood vessel (e.g., the femoral artery 26) byway of a multilumen cannula 460. Similarly, the outflow conduit 452 hasa first end 462 and a second end 464. The first end 462 of the outflowconduit 452 is connected to the outlet of the pump 432 and the secondend 464 of the outflow conduit 452 is fluidly coupled with a secondblood vessel (e.g., the descending aorta 16) by way of the multilumencannula 460.

In one embodiment, the multilumen cannula 460 includes a first lumen 466and a second lumen 468. The first lumen 466 extends from a proximal end470 of the multilumen cannula 460 to a first distal end 472. The secondlumen 468 extends from the proximal end 470 to a second distal end 474.In the illustrated embodiment, the second end 458 of the inflow conduit450 is connected to the first lumen 466 of the multilumen cannula 460and the second end 464 of the outflow conduit 452 is connected to thesecond lumen 468 of the multilumen cannula 460.

Where there is a desire for the patient 12 to be ambulatory, themultilumen cannula 460 preferably is made of material sufficientlyflexible and resilient to permit the patient 12 to be comfortably moveabout while the multilumen cannula 460 is indwelling in the patient'sblood vessels without causing any vascular trauma.

The application shown in FIG. 10 and described above results in flowfrom the first distal end 472 to the second distal end 474. Of course,the flow direction may be reversed using the same arrangement, resultingin flow from the distal end 474 to the distal end 472. In someapplications, the system 410 is applied in an arterial-arterial fashion.For example, as illustrated, the multilumen cannula 460 can be insertedinto the left femoral artery 26 of the patient 12 and guided superiorlythrough the descending aorta to one of numerous locations. In oneapplication, the multilumen cannula 460 can be advanced until the distalend 474 is located in the aortic arch 476 of the patient 12. The bloodcould discharge, for example, directly into the descending aortaproximate an arterial branch, such as the left subclavian artery ordirectly into the peripheral mesenteric artery (not shown).

The pump 432 draws blood from the patient's vascular system in the areanear the distal end 472 and into the lumen 466. This blood is furtherdrawn into the lumen of the conduit 450 and into the pump 432. The pump432 then expels the blood into the lumen of the outflow conduit 452,which carries the blood into the lumen 468 of the multilumen cannula 460and back into the patient's vascular system in the area near the distalend 474.

FIG. 11 shows another embodiment of a heart assist system 482 that issimilar to the heart assist system 410, except as set forth below. Thesystem 482 employs a multilumen cannula 484. In one application, themultilumen cannula 484 is inserted into the left femoral artery 26 andguided superiorly through the descending aorta to one of numerouslocations. Preferably, the multilumen cannula 484 has an inflow port 486that is positioned in one application within the left femoral artery 26when the cannula 484 is fully inserted so that blood drawn from the leftfemoral artery 26 is directed through the inflow port 486 into a firstlumen 488 in the cannula 484. The inflow port 486 can also be positionedin any other suitable location within the vasculature, described hereinor apparent to one skilled in the art. This blood is then pumped througha second lumen 490 in the cannula 484 and out through an outflow port492 at the distal end of the cannula 484. The outflow port 492 may besituated within, for example, a mesenteric artery 494 such that bloodflow results from the left femoral artery 26 to the mesenteric artery494. The blood could discharge, for example, directly into thedescending aorta proximate an arterial branch, such as the renalarteries, the left subclavian artery, or directly into the peripheralmesenteric artery 494, as illustrated in FIG. 11. Where there is adesire for the patient to be ambulatory, the multilumen cannula 484preferably is made of material sufficiently flexible and resilient topermit the patient 12 to comfortably move about while the cannula 484 isindwelling in the patient's blood vessels without causing any vasculartrauma.

As shown in FIG. 11, in some application and systems one or moreconduits can be positioned between the cannula 460 and a pump or othersource of liquid. In these applications and systems, any suitablestructure or technique for coupling the cannula 460 and such a conduitcan be used, including any of those described below in connection withFIGS. 17-23.

Further details of the multilumen cannula 460 may be found in U.S.patent application Ser. No. 10/078,283, filed Feb. 14, 2002, entitled AMULTILUMEN CATHETER FOR MINIMIZING LIMB ISCHEMIA. Also, any of thecannulae described herein can be altered to include any structuredescribed in U.S. patent application Ser. No. 10/706,346, filed Nov. 12,2003, entitled CANNULAE HAVING REDIRECTING TIP; U.S. application Ser.No. 11/083,042, filed Mar. 17, 2005; U.S. application Ser. No.10/686,040, filed Oct. 15, 2003; U.S. application Ser. No. 11,057,692,filed Feb. 14, 2005; U.S. application Ser. No. 10/735,413, filed Dec.12, 2003; and U.S. application Ser. No. 10/866,535, filed Jun. 10, 2004which are hereby expressly incorporated by reference in its entirety andmade a part of this specification.

FIG. 12 shows another heart assist system 510 that takes furtheradvantage of the supplemental blood perfusion and heart load reductionbenefits while remaining minimally invasive in application. The heartassist system 510 is an extracardiac pumping system that includes a pump532, an inflow conduit 550 and an outflow conduit 552. In theillustrated embodiment, the inflow conduit 550 comprises a vasculargraft. The vascular graft conduit 550 and the outflow conduit 552 arefluidly coupled to pump 532. The pump 532 is configured to pump bloodthrough the patient at subcardiac volumetric rates, and has an averageflow rate that, during normal operation thereof, is substantially belowthat of the patient's heart when healthy. In one variation, the pump 532may be a rotary pump. Other pumps described herein, or any othersuitable pump can also be used in the extracardiac pumping system 510.In one application, the pump 532 is configured so as to be implantable.

The vascular graft 550 has a first end 554 and a second end 556. Thefirst end 554 is sized and configured to couple to a non-primary bloodvessel 558 subcutaneously to permit application of the extracardiacpumping system 510 in a minimally-invasive procedure. In oneapplication, the vascular graft conduit 550 is configured to couple tothe blood vessel 558 via an anastomosis connection. The second end 556of the vascular graft 550 is fluidly coupled to the pump 532 to conductblood between the non-primary blood vessel 558 and the pump 532. In theembodiment shown, the second end 556 is directly connected to the pump532, but, as discussed above in connection with other embodiments,intervening fluid conducting elements may be interposed between thesecond end 556 of the vascular graft 550 and the pump 532. Examples ofarrangements of vascular graft conduits may be found in U.S. Pat. No.6,761,700, issued Jul. 13, 2004, entitled EXTRA-CORPOREAL VASCULARCONDUIT, which is hereby incorporated by reference in its entirety andmade a part of this specification.

FIG. 12 illustrates that the present inventive embodiment furthercomprises means for coupling the outflow conduit 552 to the vasculargraft 550, which may comprise in one embodiment an insertion site 560.In the illustrated embodiment, the insertion site 560 is located betweenthe first end 554 and the second end 556 of the vascular graft 550. Theoutflow conduit 552 preferably is coupled with a cannula 562. Thecannula 562 can take any suitable form and can be coupled with theconduit 552 by any suitable structure or technique, such as any of thetechniques or structures discussed below in connection with FIGS. 17-23.

The insertion site 560 is configured to receive the cannula 562therethrough in a sealable manner in the illustrated embodiment. Inanother embodiment, the insertion site 560 is configured to receive theoutflow conduit 552 directly. The cannula 562 includes a first end 564sized and configured to be inserted through the insertion site 560,through the cannula 550, and through the non-primary blood vessel 558.The conduit 552 has a second end 566 fluidly coupled to the pump 532 toconduct blood between the pump 532 and the blood vessel 558.

The extracardiac pumping system 510 can be applied to a patient, asshown in FIG. 12, so that the outflow conduit 552 provides fluidcommunication between the pump 532 and a location upstream or downstreamof the location where the cannula 562 enters the non-primary bloodvessel 558. In another application, the cannula 562 is directed throughthe blood vessel to a different blood vessel, upstream or downstreamthereof. Although the vascular graft 550 is described above as an“inflow conduit” and the conduit 552 is described above as an “outflowconduit,” in another application of this embodiment, the blood flowthrough the pumping system 510 is reversed (i.e., the pump 532 pumpsblood in the opposite direction), whereby the vascular graft 550 is anoutflow conduit and the conduit 552 is an inflow conduit.

FIG. 13 shows a variation of the extracardiac pumping system shown inFIG. 12. In particular, a heart assist system 570 includes an inflowconduit 572 that comprises a first end 574, a second end 576, and meansfor connecting the outflow conduit 552 to the inflow conduit 572. In oneembodiment, the inflow conduit 572 comprises a vascular graft. Theextracardiac pumping system 570 is otherwise similar to the extracardiacpumping system 510. The means for connecting the conduit 552 to theinflow conduit 572 may comprise a branched portion 578. In oneembodiment, the branched portion 578 is located between the first end574 and the second end 576. The branched portion 578 is configured tosealably receive the distal end 564 of the outflow conduit 552. Where,as shown, the first end 564 of the outflow conduit 552 comprises thecannula 562, the branched portion 578 is configured to receive thecannula 562. The inflow conduit 572 of this arrangement comprises inpart a multilumen cannula, where the internal lumen extends into theblood vessel 558. Other multilumen catheter arrangements are shown inU.S. application Ser. No. 10/078,283, incorporated by reference hereinabove.

2. Single-Site Application of Intravascular Pumping Systems

FIG. 14-16 illustrate extracardiac heart assist systems that employintravascular pumping systems. Such systems take further advantage ofthe supplemental blood perfusion and heart load reduction benefitsdiscussed above while remaining minimally invasive in application.Specifically, it is contemplated to provide an extracardiac pumpingsystem that comprises a pump that is sized and configured to be at leastpartially implanted intravascularly in any location desirable to achievethose benefits, while being insertable through a non-primary vessel.

FIG. 14 shows a heart assist system 612 that includes a pumping means614 comprising preferably one or more rotatable impeller blades 616,although other types of pumping means 614 are contemplated, such as anarchimedes screw, a worm pump, or other means by which blood may bedirected axially along the pumping means from a location upstream of aninlet to the pumping means to a location downstream of an outlet fromthe pumping means. Where one or more impeller blades 616 are used, suchas in a rotary pump, such impeller blades 616 may be supported helicallyor otherwise on a shaft 618 within a housing 620. The housing 620 may beopen, as shown, in which the walls of the housing 620 are open to bloodflow therethrough. The housing 620 may be entirely closed, if desired,except for an inlet and outlet (not shown) to permit blood flowtherethrough in a more channel fashion. For example, the housing 620could be coupled with or replaced by a cannula with a lumen that has aninner size that increases distally as discussed in U.S. patentapplication Ser. No. 10/866,535, filed Jun. 10, 2004, which is herebyincorporated by reference herein. The heart assist system 612 serves tosupplement the kinetic energy of the blood flow through the blood vesselin which the pump is positioned, e.g., the aorta 16.

The impeller blade(s) 616 of the pumping means 614 of this embodimentmay be driven in one or a number of ways known to persons of ordinaryskill in the art. In the embodiment shown in FIG. 14, the impellerblade(s) 616 are driven mechanically via a rotatable cable or drive wire622 by driving means 624, the latter of which may be positionedcorporeally (intra- or extra-vascularly) or extracorporeally. As shown,the driving means 624 may comprise a motor 626 to which energy issupplied directly via an associated battery or an external power source,in a manner described in more detail herein. It is also contemplatedthat the impeller blade(s) 616 be driven electromagnetically through aninternal or external electromagnetic drive. Preferably, a controller(not shown) is provided in association with this embodiment so that thepumping means 614 may be controlled to operate in a continuous and/orpulsatile fashion, as described herein.

Variations of the intravascular embodiment of FIG. 14 are shown in FIGS.15 and 16. In the embodiment of FIG. 15, an intrasvascular extracardiacsystem 642 comprising a pumping means 644, which may be one of severalmeans described herein. The pumping means 644 may be driven in anysuitable manner, including means sized and configured to be implantableand, if desired, implantable intravascularly, e.g., as discussed above.For a blood vessel (e.g., descending aorta) having a diameter “A”, thepumping means 644 preferably has a meaningfully smaller diameter “B”.The pumping means 644 may comprise a pump 646 having an inlet 648 and anoutlet 650. The pumping means 644 also comprises a pump drivenmechanically by a suitable drive arrangement in one embodiment. Althoughthe vertical arrows in FIG. 15 illustrate that the pumping means 644pumps blood in the same direction as the flow of blood in the vessel,the pumping means 644 could be reversed to pump blood in a directiongenerally opposite of the flow in the vessel.

In one embodiment, the pumping means 644 also includes a conduit 652 inwhich the pump 646 is housed. The conduit 652 may be relatively short,as shown, or may extend well within the designated blood vessel or eveninto an adjoining or remote blood vessel at either the inlet end, theoutlet end, or both. The intravascular extracardiac system 642 mayfurther comprise an additional parallel-flow conduit, as discussed belowin connection with the system of FIG. 16.

The intrasvascular extracardiac system 642 may further comprise inflowand/or outflow conduits or cannulae (not shown) fluidly connected to thepumping means 644, e.g., to the inlet and outlet of pump 646. Anysuitable conduit or cannula can be employed. For example, a cannuladefining a lumen with an inner size that increases distally, asdiscussed herein or in the applications incorporated by reference hereincould be coupled with an intrasvascular extracardiac system.

In another embodiment, an intrasvascular pumping means 644 may bepositioned within one lumen of a multilumen catheter so that, forexample, where the catheter is applied at the left femoral artery, afirst lumen may extend into the aorta proximate the left subclavian andthe pumping means may reside at any point within the first lumen, andthe second lumen may extend much shorter just into the left femoral orleft iliac. Such a system is described in greater detail in U.S.application Ser. No. 10/078,283, incorporated by reference herein above.

FIG. 16 shows a variation of the heart assist system of FIG. 15. Inparticular the intravascular system may further comprise an additionalconduit 660 positioned preferably proximate the pumping means 644 toprovide a defined flow path for blood flow axially parallel to the bloodflowing through the pumping means 644. In the case of the pumping means644 of FIG. 16, the means comprises a rotatable cable 662 having blooddirecting means 664 supported therein for directing blood axially alongthe cable. Other types of pumping means are also contemplated, ifdesired, for use with the additional conduit 660.

The intravascular extracardiac system described herein may be insertedinto a patient's vasculature in any means known by one of ordinary skillor obvious variant thereof. In one method of use, such a system istemporarily housed within a catheter that is inserted percutaneously, orby surgical cutdown, into a non-primary blood vessel and advancedthrough to a desired location. The catheter preferably is then withdrawnaway from the system so as not to interfere with operation of thesystem, but still permit the withdrawal of the system from the patientwhen desired. Further details of intravascular pumping systems may befound in U.S. patent application Ser. No. 10/686,040, filed Oct. 15,2003, which is hereby incorporated by reference herein in its entirety.

C. Potential Enhancement of Systemic Arterial Blood Mixing

One of the advantages of the present invention is its potential toenhance mixing of systemic arterial blood, particularly in the aorta.Such enhanced mixing ensures the delivery of blood with higheroxygen-carrying capacity to organs supplied by arterial side branchesoff of the aorta. A method of enhancing mixing utilizing the presentinvention preferably includes taking steps to assess certain parametersof the patient and then to determine the minimum output of the pumpthat, when combined with the heart output, ensures turbulent flow in theaorta, thereby enhancing blood mixing.

Blood flow in the aortic arch during normal cardiac output may becharacterized as turbulent in the end systolic phase. It is known thatturbulence in a flow of fluid through pipes and vessels enhances theuniform distribution of particles within the fluid. It is believed thatturbulence in the descending aorta enhances the homogeneity of bloodcell distribution in the aorta. It is also known that laminar flow ofviscous fluids leads to a higher concentration of particulate in thecentral portion of pipes and vessels through which the fluid flows. Itis believed that, in low flow states such as that experienced duringheart failure, there is reduced or inadequate mixing of blood cellsleading to a lower concentration of nutrients at the branches of theaorta to peripheral organs and tissues. As a result, the blood flowinginto branch arteries off of the aorta will likely have a lowerhematocrit, especially that flowing into the renal arteries, the celiactrunk, the spinal arteries, and the superior and inferior mesentericarteries. That is because these branches draw from the periphery of theaorta The net effect of this phenomenon is that the blood flowing intothese branch arteries has a lower oxygen-carrying capacity, becauseoxygen-carrying capacity is directly proportional to both hematocrit andthe fractional O₂ saturation of hemoglobin. Under those circumstances,it is very possible that these organs will experience ischemia-relatedpathology.

The phenomenon of blood streaming in the aorta, and the resultantinadequate mixing of blood resulting in central lumenal concentration ofblood cells, is believed to occur when the Reynolds number (NR) for theblood flow in the aorta is below 2300. To help ensure that adequatemixing of blood will occur in the aorta to prevent blood cells fromconcentrating in the center of the lumen, a method of applying thepresent invention to a patient may also include steps to adjust theoutput of the pump to attain turbulent flow within the descending aortaupstream of the organ branches; i.e., flow exhibiting a peak Reynoldsnumber of at least 2300 within a complete cycle of systole and diastole.Because flow through a patient is pulsatile in nature, and notcontinuous, consideration must be given to how frequently the blood flowthrough the aorta has reached a certain desired velocity and, thus, adesired Reynolds number. The method contemplated herein, therefore,should also include the step of calculating the average Womersley number(N_(W)), which is a function of the frequency of the patient's heartbeat. It is desired that a peak Reynolds number of at least 2300 isattained when the corresponding Womersley number for the same blood flowis approximately 6 or above.

More specifically, the method may comprise calculating the Reynoldsnumber for the blood flow in the descending aorta by determining theblood vessel diameter and both the velocity and viscosity of the fluidflowing through the aorta. The Reynolds number may be calculatedpursuant to the following equation:

$N_{R} = \frac{V \cdot d}{v}$

where: V=the velocity of the fluid; d=the diameter of the vessel; andυ=the viscosity of the fluid. The velocity of the blood flowing throughthe aorta is a function of the cross-sectional area of the aorta and thevolume of flow therethrough, the latter of which is contributed both bythe patient's own cardiac output and by the output of the pump of thepresent invention. Velocity may be calculated by the following equation:

$V = \frac{Q}{\pi \; r^{2}}$

where Q=the volume of blood flowing through the blood vessel per unittime, e.g., the aorta, and r=radius of the aorta. If the relationshipbetween the pump output and the velocity is already known orindependently determinable, the volume of blood flow Q may consist onlyof the patient's cardiac output, with the knowledge that that outputwill be supplemented by the subcardiac pump that is part of the presentinvention. If desired, however, the present system can be implementedand applied to the patient first, before calculating Q, which wouldconsist of the combination of cardiac output and the pump output.

The Womersley number may be calculated as follows:

N _(W)=r√{square root over (2πω/υ)}

where r is the radius of the vessel being assessed, ω is the frequencyof the patient's heartbeat, and υ=the viscosity of the fluid. For a peakReynolds number of at least 2300, a Womersley number of at least 6 ispreferred, although a value as low as 5 would be acceptable.

By determining (i) the viscosity of the patient's blood, which isnormally about 3.0 mm²/sec (kinematic viscosity), (ii) the cardiacoutput of the patient, which of course varies depending upon the levelof CHF and activity, and (iii) the diameter of the patient's descendingaorta, which varies from patient to patient but is about 21 mm for anaverage adult, one can determine the flow rate Q that would result in avelocity through the aorta necessary to attain a Reynolds number of atleast 2300 at its peak during the patient's heart cycle. Based upon thatdetermination of Q, one may adjust the output of the pump of the presentinvention to attain the desired turbulent flow characteristic throughthe aorta, enhancing mixing of the blood therethrough.

One may use ultrasound (e.g., echocardiography or abdominal ultrasound)to measure the diameter of the aorta, which is relatively uniform indiameter from its root to the abdominal portion of the descending aorta.Furthermore, one may measure cardiac output using a thermodilutioncatheter or other techniques known to those of skill in the art.Finally, one may measure viscosity of the patient's blood by using knownmethods; for example, using a capillary viscosimeter. It is expectedthat in many cases, the application of this embodiment of the presentmethod will provide a basis to more finely tune the system to moreoptimally operate the system to the patient's benefit. Other methodscontemplated by the present invention may include steps to assess otherpatient parameters that enable a person of ordinary skill in the art tooptimize the present system to ensure adequate mixing within thevascular system of the patient.

Alternative inventive methods that provide the benefits discussed hereininclude the steps of, prior to applying a shape change therapy, applyinga blood supplementation system (such as one of the many examplesdescribed herein) to a patient, whereby the methods are designed toimprove the ability to reduce the size and/or wall stress of the leftventricle, or both ventricles, thus reducing ventricular loading.Specifically, one example of such a method comprises the steps ofproviding a pump configured to pump blood at subcardiac rates, providinginflow and outflow conduits configured to fluidly communicate withnon-primary blood vessels, fluidly coupling the inflow conduit to anon-primary blood vessel, fluidly coupling the outflow conduit to thesame or different (primary or non-primary) blood vessel and operatingthe subcardiac pump in a manner, as described herein, to reduce the loadon the heart, wherein the fluidly coupling steps may compriseanastomosis, percutaneous cannulazation, positioning the distal end ofone or both conduits within the desired terminal blood vessel or anycombination thereof. The method further comprises, after sufficientreduction in ventricular loading, applying a shape change therapy in theform of, for example, a cardiac reshaping device, such as those referredto herein, or others serving the same or similar function, for thepurpose of further reducing the size of and/or wall stress on one ormore ventricles and, thus, the heart, and/or for the purpose ofmaintaining the patient's heart at a size sufficient to enhance recoveryof the patient's heart.

II. Systems and Techniques for Priming a Fluid Circuit

As discussed above, a variety of systems can be applied to a patient toprovide an efficacious treatment, such as one offloading the heart inconnection with congestive heart failure. It is generally preferred thatsuch systems are coupled with a patient in a manner that minimizes orcompletely prevents the introduction of embolic matter, e.g., particlesor gases, into the blood stream. It would be advantageous to providestructures and techniques for such a coupling or connection, whichtechniques and structures are sometimes referred to herein as “priming.”

FIGS. 17-23 illustrate a variety of structures useful for priming fluidcircuits. As discussed further below, such structures can be deployedfor medical treatments that involve circulating blood, components ofblood, or other bodily fluids, and these structures also are useful forproviding a fluid flow circuit connection with little or no foreignmatter outside medical contexts.

FIG. 17 shows one embodiment of a system 700 for priming a liquidcircuit. As discussed further below, the system 700 can be applied toany liquid circuit, including circuits designed to convey biologicalfluid, e.g., whole blood or any subset thereof, such as plasma. Thesystem 700 initially is discussed in connection with some components ofthe heart assist system 10 but also is applicable to the other heartassist systems described herein and other systems that may be similar.However, the system 700 can be used in connection with any of thesystems disclosed herein and with other fluid circuits as discussedbelow. FIG. 17 illustrates that in one embodiment, the system 700includes a tube assembly 702 and a cannula assembly 704.

The tube assembly 702 includes a tube and a tube connector 706. In theillustrated embodiment, the tube comprises the outflow conduit 50, whichcan be coupled with the pump 36, of the system 10 as illustrated inFIG. 1. The tube connector 706 includes a housing 708 in one embodimentthat can be made of a suitable material such as a polycarbonate, PVC,acrylic, polystyrene, or another similar material. A lumen 710 can beformed in the housing 708 and can be provided with a first housingcross-sectional area 712. In some embodiments, the housing 708 has or iscoupled with (e.g., fluidly coupled with) one or multiple lumens.Preferably the lumen 710 is a main lumen where the housing 708 has aplurality of lumens. As used herein, the term “main lumen” is a broadterm that includes configurations where the lumen 710 is the largestlumen formed in or connected to the largest lumen in the housing 708.The term “main lumen” also includes a lumen that is the primary lumenused to conduct fluid during the majority of the use of the conduit 50,e.g., a lumen not closed off during operation of the system 10.

The tube connector 706 and the outflow conduit 50 can be coupled in anysuitable manner. For example, an adhesive can be used to join thesecomponents together. In the illustrated embodiment, a junction 714 isprovided between the outflow conduit 50 and the housing 708. Thejunction 714 can be a butt-end junction, as shown. In anotherembodiment, at least a portion of the second end 58 of the conduit 50 isinserted into the housing 708. Where the second end 58 of the conduit 50is inserted into the housing 708, one end of the housing preferablyincludes an enlarged lumen and the opposite end of the housing 708includes a smaller lumen. Preferably, the enlarged lumen of the housing708 is large enough to receive the second end 58 of the conduit 50, suchthat a seamless blood flow path is provided between the smaller lumenend of the housing 708 and the lumen of the conduit 50. Any suitabletechnique can be used for connecting the conduit 50 to the housing 708where the housing is configured to have a portion of the conduitinserted thereinto. For example, an adhesive can be used to secure thesecond end 58 of the conduit 50 within the housing 708. At least one ofthe tube assembly 702 and the cannula assembly 704 and other similarstructures can be made as single unitary structures that are notassembled by a practitioner.

The housing 708 also comprises a first port 716 and a membrane 718 thatextends across the first port 716. The membrane 718 can be coupled withthe housing 708 in any suitable manner. For example, the membrane 718can be secured to the first port 716 by an adhesive or integrally formedtherewith. In other embodiments discussed below, a screw cap is used tosecure the membrane 718 to the housing 708. As discussed further below,a screw cap and a gasket or other suitable seal can be provided tosubstantially reduce or completely prevent fluid from inadvertentlyleaking out of the tube connector 706.

In one embodiment, the membrane 718 is permeable to gas. The gaspermeable embodiments of the membrane 718 are advantageous for oneprimary technique wherein a liquid is forced into the housing 708 andthe liquid thereafter flows toward the membrane 718. As the liquid flowstoward the membrane 718, any gas found in the housing will be forced outof the housing through the membrane. The membrane 718 could also beconfigured to permit at least one component of the liquid to flowtherethrough, while preventing other components of the liquid fromflowing therethrough. In this sense, the membrane 718 can also perform afiltering function. The membrane 718 can be formed of a high densityfiber material in some arrangements, e.g., polyethylene.

In one embodiment, the housing 708 includes a second port 720 that isconfigured to couple with the outflow conduit 50 or of another tube. Asdiscussed above, at least a portion of the second end 58 can be coupledwith the housing 708 or inserted into the housing, e.g., through thesecond port 720.

In one embodiment, the housing 708 also includes a third port 722. Insome applications, the third port 722 is configured to couple with asource of liquid. For example, a tube 724 that can be configured toconvey a suitable liquid can be coupled with the third port 722. Whereused, the tube 724 includes a first end 726, a second end 728, and alumen 730 extending therebetween. The lumen 730 is sometimes referred toherein as a “secondary” lumen. In some arrangements, the housing 708includes a plurality of side ports that each can be configured as athird port 722, as shown in FIG. 20.

In one technique for priming a system, the first end 726 is coupled witha source of liquid and the second end 728 is in fluid communication withthe lumen 710. As discussed above and further below, liquid can beforced from the first end 726 to the second end 728 through the lumen730 and into the lumen 710. In some techniques, the fluid can further beforced out of the first port 716 through the membrane 718. Where thesystem 700 is used in a biological system, e.g., in connection with thesystem 10 or the other systems described herein, or other cardiovasculartreatments, the first end 726 preferably is coupled with a source ofbio-compatible liquid, such as saline.

In some embodiments, it is advantageous to provide a seamless, or smoothlumen throughout the fluid circuit. For example, in connection withcirculating blood, seamless lumens can minimize damage to blood cellsthat can occur when blood cells are forced to flow along a path that isnot seamless or smooth, e.g., a discontinuous flow path. In onearrangement, the system 700 comprises an arrangement that minimizes oreliminates discontinuities therein. One arrangement for minimizing oreliminating discontinuities provides an internal surface 732 formedinside the housing 708. The internal surface 732 preferably is acircumferential surfaces that extends inwardly from an inner wall 734 ofthe housing 708 toward a longitudinal axis of the lumen 710.

As discussed further below, the surface 732 can be configured to engagean end surface of the cannula assembly 704, whereby discontinuities in ablood flow path or other artifacts preventing seamless or smooth bloodflow over the surface 732 can be eliminated or reduced to a clinicallyinsignificant level. In one embodiment, the internal surface 732 isangled relative to the longitudinal axis of the lumen 710 such that thesurface 732 has a distal region 735 and a proximal region 736.

In one embodiment, at least the region of the housing 708 that includesthe surface 732 is configured to provide a seal along the point ofconnection between the tube assembly 702 and the cannula assembly 704.One technique for providing a seal involves configuring the surface 732to accommodate at least a portion of the cannula assembly 704, e.g., tobe deform when the cannula assembly 704 is urged into contact with thesurface 732. Such deformation or accommodation can eliminate or minimizevoids between these structures. In one embodiment, the surface 732comprises a soft material that enhances sealing along the surface 732and that accommodates at least a portion of the cannula assembly 704.Silicone is one material that is soft enough to deform to prevent suchvoids.

In one embodiment, the tube assembly 702 is configured such that themembrane 718 is not permanently fixed to the housing 708. Thisarrangement enables replacement of the membrane 718, or reuse of atleast a portion of the tube assembly 702 where the system 700 is notconfigured as a disposable system. For example, in many non-medicalapplications, the conditions under which a system similar to the system700 may require expensive materials or construction techniques. In suchcases, the cost of the components of the system will increase. Also, insome non-medical applications there may be little or no risk ofcontamination associated with the reuse of a liquid priming system. Inthese and other similar contexts, reuse of the priming system iscontemplated. In many medical applications, the components of the system700 can be disposable, e.g., made of low-cost materials such as plastic.Disposable systems provide more assurance that the system will besterile and will not introduce bacteria or contaminants into thebloodstream of the patient.

In one embodiment, the tube assembly 702 includes a removable cap 738.The removable end cap 738 can be coupled with the housing 708 adjacentto the first port 716. In one embodiment, the end cap 738 includes anengagement portion 740 that extends along the longitudinal axis of thelumen 710 when the cap 738 is coupled with the housing 708 and an endportion 742 that extends transversely engagement portion. The cap 738 isconfigured to engage the housing 708 adjacent to the first port 716. Forexample, in one embodiment a recess 744 is defined within the end cap738. The recess 744 can be defined between the engagement portion 740and the end portion 742. In one embodiment, the recess 744 is largerthan the outer size of the housing 708. In one embodiment, theengagement portion 740 includes internal threads 746 that extend betweenthe end portion 742 and an end of the engagement portion 740 oppositethe end portion. The threads 746 are configured to mate withcorresponding external threads 748 formed on the housing 708 adjacent tothe first port 716. The threads 746, 748 enable the end cap 738 to beadvanced onto the housing 708 and secured thereon.

In one technique, the membrane 718 is configured to be positionedbetween the housing 708 and the end cap 738 and to be secured therein byadvancing the end cap 738 onto the housing 708 using the threads 746,748. For example, the membrane 718 can be positioned between the endportion 742 and an end surface 750 of the housing 708 adjacent to thefirst port 716.

In one arrangement, the membrane 718 comprises a portion of a membraneassembly 770 that is configured to be secured between the end cap 738and the housing 708. The membrane assembly 770 preferably is configuredto be securely positioned within the tube assembly 702. In onearrangement, the membrane assembly 770 includes a seal member 772configured to be positioned between the surfaces 742, 750. The sealmember 772 can be an O-ring or other similar compressible member. In onearrangement, the membrane 718 is attached to the seal member 772, e.g.,by a suitable adhesive.

The cannula assembly 704 comprises a cannula 800, which may be similarto the inflow cannula 60 shown in FIG. 1, and a cannula connector 802.The cannula 800 includes a first end 804 and a second end 806 configuredto couple with a source of liquid to be conveyed in the circuit. Asdiscussed further below, the first end 804 is coupled with the cannulaconnector 802 in a suitable fashion. The second end 806 is shown as astraight, angled member. As discussed in U.S. application Ser. No.10/706,346, filed Nov. 12, 2003, which is hereby incorporated byreference herein, the second end 806 can take a variety of shapes andconfigurations that advantageously direct blood being delivered into orremoved from the vasculature. The system 700 can be used in connectionwith any of these cannula designs. The cannula 800 defines a portion ofa cannula lumen 808 that has a first cross-sectional area. The firstcross-sectional area is located generally distally of the cannulaconnector 802 and can be generally constant along the length of thelumen 808 or can vary along this length, e.g., increasing in size towardthe second end 806. A variety of configurations for the cannula 800 andtips therefore are described in U.S. application Ser. No. 10/866,535,filed Jun. 10, 2004.

The cannula connector 802 includes a piercing member 814. In somearrangement, a portion of the blood flow path through the cannulaassembly 704 is located in the cannula connector 802, e.g., within thepiercing member 814. In one embodiment, the cannula lumen 800 has asecond cross-section or cross-sectional area adjacent or within thepiercing member 814. In one embodiment, the second cross-sectional areais substantially the same as the first cross-sectional area. Thisarrangement provides a seamless lumen, which encourages smooth bloodflow between the lumen 808 in the cannula 800 and the cannula connector802. Smooth flow reduces or eliminates perturbations in the flow thatcould create biological reactions within the blood, such as thrombosis.In one arrangement, the flow is substantially laminar from within thecannula 800 to within the cannula connector 802. As discussed above, theterms “seamless” and “seamless lumen” are broad terms describing a bloodflow path or a portion of a blood flow path that is configured topromote a smooth flow, a laminar flow, or any other fluid flow regimethat prevents or minimizes damage to a delicate fluid. Seamless lumenscan be provided in unitary extrusions or in assemblies that whenassembled do not present significant steps in the flow patch. Forexample, an assembly of two structures that have lumen segments that canbe joined at mating edges are seamless if they present a step of lessthan a percentage of the size of the lumen, for example less than about10 percent. A lesser step as a percentage of size would perform evenbetter in some arrangements, e.g., less than about 5 percent. A evensmaller step as a percentage of size would perform even better in somearrangements, e.g., less than about 2 percent. In one arrangement, ablood flow lumen is provided that has an inner diameter of about 0.25inches and the size of a step can be maintained to less than about 0.005inches (about 0.13 mm).

In the embodiment of FIG. 17, the cannula connector 802 has a secondcross-sectional area within the piercing member 814 that is larger thanthe cross-sectional area within the cannula 800. The cross-sectionalarea change can be provided by a transition section 816 located betweenthe piercing member 814 and the cannula 800. The transition section 816has varying cross-sectional area along its length in one embodiment. Thevariation in cross-sectional area can be generally constant, or linear,or can vary in any other suitable fashion to transition the blood fromflowing in the within the cannula 800 to flowing within the cannulaconnector 802. By increasing the size of the lumen 808 defined withinthe cannula assembly 704, the transition from the cannula assembly 704to the lumen 710 can be seamless, reducing the chance of thrombosis orother negative flow-perturbation-induced reaction in the blood,biologic, or other delicate fluid.

In some applications, it is preferred that there not be a transition inthe blood flow characteristics within the cannula connector 802. Forexample, it might be advantageous in some applications to provide aconstant lumen size from the proximal end of the conduit 50, through thesystem 700, and to the distal end of the cannula 800. In otherarrangements, it might be advantageous to provide only an increase inthe lumen size between the cannula connector 802 and the distal end ofthe cannula 800. In such arrangements, the cannula connector 802 couldbe configured with a substantially constant cross-sectional area fromits proximal end to its distal end. This arrangement is shown in FIGS.18, 19, and 23.

In some priming techniques, discussed further below, it is beneficial tobe able to selectively close a portion of a blood flow path. Forexample, the lumens at least partially defined in any of the cannula800, the cannula connector 802, the conduit 50, and the tube connector706 could selectively be closed to limit or prevent blood flow at leasttemporarily. In one technique discussed in more detail below, thetransition section 816 is configured to be compressible such that thelumen in the transition section 816 can be selectively closed toblood-flow. As discussed further below, closing the lumen prevents anexcessive amount of fluid to flow distal to proximal in the cannula 800.In a medical application, the distal end of the cannula 800 can becoupled with an artery under pressure prior to the system 700 beingjoined. Selective closing of the lumen 808 prevents excessive amounts ofblood from being lost.

The piercing member 814 preferably is configured to pierce the membrane718 upon joining the cannula connector 802 to the tube connector 706.For example, the piercing member 814 can be provided with a tip 820 thatis configured such that will perforate the membrane 718 if the tip 820is advanced toward the tube assembly 702. The tip 820 can be configuredas a sharp surface or point. In one arrangement, the tip 820 isconfigured to be advanceable into the tube connector 706, for example byhaving an outer size that is slightly smaller than the inner sizedefined by the inner wall 734. In one arrangement, the tip 820 isconfigured with an inclined surface that matches the internal surface732. The internal surface 732 can be made of a compressible or resilientmaterial. When the tip 820 is advanced into engagement with the surface732, the surface deforms such that few or no voids are located betweenthe surface 732 and the tip 820. The elimination of voids between thesestructures reduces the likelihood that blood will escape from thepriming system 700. Eliminating voids at the surface near the lumen nearthe surface also provides a seamless lumen for advantageous flowcharacteristics.

As discussed above, the system 700 advantageously minimizes oreliminates flow disruption to prevent damage to the fluid flowing in thesystem when the fluid is delicate. The system 700 can be configured witha structure to assist the user in coupling the tube connector 706 andthe cannula connector 802. For example, in some arrangements where thesurface 732 is compressible if the tip 820 is advanced to far relativeto the tube connector 706, the surface 732 might be deformed into theblood flow path. This condition is sometimes referred to herein as“overinsertion.” To prevent or minimize overinsertion, the system 700can include a stop member 824. The stop member 824 can take any suitableform and can be located in any convenient location on the system. Forexample, the stop member 824 can be a shoulder on the cannula connector802 that includes an annulus that contacts or abuts an end surface ofthe tube connector 706 when the cannula connector 802 is sufficiently,but not overly, inserted into the tube connector 706. This arrangementis illustrated in FIG. 17.

Rather than a shoulder, the stop member 824 can be configured as a ringor annulus mounted on an outer surface of the cannula connector 824, asillustrated in FIGS. 18, 19, and 23. The ring or annular arrangementfunctions in a similar fashion to the shoulder of FIG. 17. Inparticular, the cannula connector 802 can be advanced into the tubeconnector 706 until the ring or annulus configuration stop member 824 isin contact with an end surface of the tube connector 706. This conditionis illustrated in FIG. 18. The location of the ring or annulus stopmember is such that overinsertion will not occur.

In some applications, the system 700 can be coupled with a cannula byinserting the cannula connector 802 into a proximal end of the cannula.The cannula connector 802 can be configured to engage the proximal endof the cannula for such application. For example, one or a plurality ofengagement features 834 can be provided near the distal end of thecannula connector 802. The engagement features 834 can be ridgesextending outwardly from an outer surface of the cannula connector 802near the distal end thereof. In another embodiment, the engagementfeature 834 can be a recess into which a portion of a cannula 800 cansubside when inserted over the distal end of the cannula connector 802.

In one embodiment, the priming system 700 includes a locking device 850for securely connecting the tube assembly 702 and the cannula assembly704 together. The locking device 850 can take any suitable form. In oneembodiment one or more lateral extensions 852A are provided on the tubeconnector 706 and one or more lateral extensions 852B are provided onthe cannula connector 802. The lateral extensions 852A, 852B areconfigured to have a force directed parallel to the longitudinal axis ofthe housing 708 applied thereto to prevent the connectors 706, 802 frombecoming disengaged inadvertently. The force can be applied by a clampor other suitable force generating device.

In another embodiment illustrated in FIG. 19, the locking device 850comprises one or more prongs 856 provided on the end cap 738. The prongs768 are configured to engage a portion of the cannula assembly 704 tolock the cannula assembly and the tube assembly 702 together. Forexample, the prongs 856 can be configured to engage the ring orannulus-type stop member 824 illustrated in FIG. 19. The engagement ofthe prongs with the member 824 can be provided by configuring the prongsto define an inner dimension that is slightly smaller than an outerdimension (e.g., the perimeter or circumference) of the stop member 824.Accordingly, when the stop member 824 is advanced past the distal endsof the prongs 856, the prongs are deflected laterally outwardly.

In one embodiment, the prongs 856 have hook-like distal ends such thatafter then cannula connector 802 is sufficiently advanced the hook endsare distal of the stop member 824 and thereby prevent the stop member824 from inadvertently being moved distally out of the tube connector706. The systems described above can be used in a method of priming ablood circuit that includes the pump 32, the inflow conduit 50 (or otherpump tube) having a pump tube lumen fluidly coupled with the pump 32.The membrane 718, which is gas permeable, extends across the pump tubelumen 710. The system also includes the cannula 800 having a cannulalumen that extends between the first and second ends 804, 806. Apiercing structure 814, which can include the tip 820, is adjacent tothe first end 804. In one technique, a biocompatible liquid is forcedinto the pump tube lumen 710 at a location between the membrane 718 andthe pump 34 to pressurize the pump tube lumen 710. The biocompatibleliquid forces gas in the pump tube lumen 710 out of the lumen 710through the membrane 718. Thus, the lumen 710 can be substantiallypurged of gas by the biocompatible liquid. Thereafter, the piercingstructure 814 can be used to pierce the membrane 718 such that thecannula lumen 808 and the pump tube lumen 710 are in fluidcommunication.

In some arrangements and techniques, the pierced portion of the membrane718 is forced between an outer wall of the cannula connector and theinner wall 734 of the housing 708 when the cannula connector is insertedinto the pump tube connector 706. This arrangement and techniqueadvantageously traps the membrane 718 out of the fluid flow path toprevent the introduction of the membrane or at least substantial, largeportions thereof, from entering the flow. In some techniques, thepiercing member 814 is configured so that upon connection, the membrane718 is opened to create a flap that is substantially sandwiched betweenan outer wall of the cannula connector and the inner wall 734 of thepump tube connector 706.

In one arrangement and technique, the housing 708 is configured suchthat access to the third port 722 is blocked by an outer wall of thecannula connector 802 when the cannula connector is inserted into thepump tube connector 706. This advantageously prevents fluid in the fluidflow path from escaping through the third port 722 and also preventscontaminants from entering the blood flow path through the third port.

In one variation, the cannula lumen 808 is pressurized prior to piercingthe membrane 718 such that a liquid in the cannula lumen flows out ofthe first end of the cannula lumen. As discussed above, the amount ofliquid that flows out of the cannula lumen 808 can be limited by a clampor other structure for selectively closing off the lumen. In sometechniques, the presence of fluid in the lumen can be checked byloosening a clamping structure selectively applied to a portion of thecannula assembly 704. Permitting a small volume of fluid to escape fromthe proximal end of the cannula assembly 704 is one technique foreliminating gas from the cannula assembly. This technique generally isperformed prior to connecting the tube assembly 702 and the cannulaassembly 704 together.

In another technique, the cannula connector 802 and the pump tubeconnector 706 are locked together to prevent these structures frominadvertently becoming disengaged during the procedure, as discussedabove.

Although the foregoing invention has been described in terms of certainpreferred embodiments, other embodiments will be apparent to those ofordinary skill in the art. Additionally, other combinations, omissions,substitutions and modification will be apparent to the skilled artisan,in view of the disclosure herein. Accordingly, the present invention isnot intended to be limited by the recitation of the preferredembodiments, but is instead to be defined by reference to the appendedclaims.

1. A system for priming a blood-flow circuit coupled with a pump,comprising: a pump tube assembly comprising a pump tube and a pump tubeconnector, the connector comprising a housing with a lumen therethroughhaving a housing cross-sectional area, the housing also comprising afirst port, a membrane extending across the first port, a second portconfigured to couple with the pump tube, and a third port configured tocouple with a source of biocompatible liquid; and a cannula assemblycomprising: a cannula comprising a first end and a second end configuredto couple with a blood vessel, the cannula defining a portion of acannula lumen having a first cross-sectional area; and a cannulaconnector comprising a piercing member that defines a portion of thecannula lumen having a second cross-sectional area, the secondcross-sectional area being substantially the same as the firstcross-sectional area, the piercing member configured to pierce themembrane upon joining the cannula connector to the pump tube connector.2. The system of claim 1, wherein the piercing member comprises a firstsurface and the pump tube connector comprises a second surface, thefirst and second surfaces configured to engage so as to provide aseamless lumen within the pump tube connector at least at the locationwhere the first and second surfaces engage.
 3. The system of claim 1,wherein the membrane is permeable to gas.
 4. The system of claim 1,further comprising a source of biocompatible liquid configured to couplewith the third port.
 5. The system of claim 4, wherein the biocompatibleliquid comprises saline.
 6. The system of claim 1, wherein the piercedportion of the membrane is forced between an outer wall of the cannulaconnector and an inner wall of the pump tube connector when the cannulaconnector is inserted into the pump tube connector.
 7. The system ofclaim 1, wherein the piercing member is configured so that uponconnection, the membrane is opened to create a flap that issubstantially sandwiched between an outer wall of the cannula connectorand an inner wall of the pump tube connector.
 8. The system of claim 1,wherein the second end of the cannula is configured to fluidly couplewith a blood vessel.
 9. A method of priming a blood circuit comprising apump, a pump tube having a pump tube lumen fluidly coupled with thepump, a gas permeable membrane extending across the pump tube lumen, acannula having a cannula lumen that extends between a first end and asecond end, and a piercing structure adjacent to the first end, themethod comprising: forcing a biocompatible liquid into the pump tubelumen at a location between the gas permeable membrane and the pump topressurize the pump tube lumen and to force gas in the pump tube lumenthrough the membrane; and piercing the membrane with the piercingstructure such that the cannula lumen and the pump tube lumen are influid communication.
 10. A connector system for use in priming a bloodcircuit having a pump, a conduit having a first end coupled with thepump and a second end, a cannula having a first end and a second endconfigured to fluidly couple with a blood vessel, and a cannula lumenextending therebetween, the system comprising: a first connectorconfigured to couple with the second end of the conduit, the firstconnector comprising a gas permeable membrane, a main lumen extendingfrom the gas permeable membrane, and a secondary lumen having a firstend configured to couple with a source of bio-compatible liquid and asecond end in fluid communication with the main lumen; and a secondconnector configured to couple with the first end of the cannula, thesecond connector having an end configured to be inserted through the gaspermeable membrane into the first connector, whereby fluid communicationcan be established between the main lumen of the first connector and thecannula lumen.
 11. The system of claim 10, wherein the first connectorhas an internal surface and the second connector has an end surfaceconfigured to engage with the internal surface of the first connector.12. A connector system for use in priming a fluid circuit having a pump,a conduit having a first end coupled with the pump and a second end, acannula having a first end and a second end configured to fluidly couplewith a first fluid source, and a cannula lumen extending between thefirst and second ends of the cannula, the system comprising: a firstconnector configured to couple with the second end of the conduit, thefirst connector comprising a gas permeable membrane, a main lumenextending from the gas permeable membrane, and a second lumen having afirst end configured to couple with a second fluid source and a secondend in fluid communication with the main passage; and a second connectorconfigured to couple with the first end of the cannula, the secondconnector having an end configured to be inserted through the gaspermeable membrane into the first connector, whereby fluid communicationcan be established between the main passage of the first connector andthe cannula lumen.
 13. A system for priming a liquid circuit,comprising: a tube assembly comprising a tube and a tube connector, theconnector comprising a housing with a lumen therethrough having ahousing cross-sectional area, the housing also comprising a first port,a membrane extending across the first port, a second port configured tocouple with the tube, and a third port configured to couple with asource of liquid; and a cannula assembly comprising: a cannulacomprising a first end and a second end configured to couple with asource of liquid to be conveyed in the circuit, the cannula defining aportion of a cannula lumen having a first cross-sectional area; and acannula connector comprising a piercing member that defines a portion ofthe cannula lumen having a second cross-sectional area, the secondcross-sectional area being substantially the same as the firstcross-sectional area, the piercing member configured to pierce themembrane upon joining the cannula connector to the tube connector.